EP2392264B1 - Störechofilterung mit Eigenvektoren in einem Ultraschallsystem - Google Patents

Störechofilterung mit Eigenvektoren in einem Ultraschallsystem Download PDF

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Publication number
EP2392264B1
EP2392264B1 EP11177746.2A EP11177746A EP2392264B1 EP 2392264 B1 EP2392264 B1 EP 2392264B1 EP 11177746 A EP11177746 A EP 11177746A EP 2392264 B1 EP2392264 B1 EP 2392264B1
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Prior art keywords
eigenvectors
doppler signals
signals
doppler
clutter signal
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English (en)
French (fr)
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EP2392264A1 (de
Inventor
Seong Ho Song
Tae Yun Kim
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Samsung Medison Co Ltd
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Samsung Medison Co Ltd
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Priority claimed from KR1020090128886A external-priority patent/KR101117900B1/ko
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8979—Combined Doppler and pulse-echo imaging systems
    • G01S15/8981—Discriminating between fixed and moving objects or between objects moving at different speeds, e.g. wall clutter filter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/488—Diagnostic techniques involving Doppler signals

Definitions

  • the present disclosure relates to ultrasound signal processing, and more particularly to clutter signal filtering upon Doppler signals using eigenvectors in an ultrasound system.
  • an ultrasound system has been extensively used in the medical field due to its non-invasive and non-destructive nature.
  • Modem high-performance ultrasound imaging diagnostic systems and techniques are commonly used to produce two- or three-dimensional ultrasound images of internal features of patients.
  • the ultrasound system operates in various image modes such as a brightness mode, a Doppler mode and the like to acquire ultrasound images for diagnosis.
  • the ultrasound system provides a color flow image visualizing velocities of moving objects such as blood flow, heart, etc.
  • the color flow image may be formed based on Doppler signals obtained by alternately transmitting and receiving ultrasound signals to and from a target object at a pulse repetition frequency (PRF).
  • the Doppler signals may include low frequency signals (the so-called clutter signals) due to the motion of a cardiac wall or valve of a heart.
  • the clutter signals may have amplitudes, which are over 100 times than those of pure Doppler signals indicative of velocities of the blood flow.
  • the clutter signals may be an obstacle to accurately detecting velocities of the blood flow. Thus, it is required to remove the clutter signals from the Doppler signals for accurate velocity detection of the blood flow.
  • the eigenvector-based clutter filtering is carried out by reflecting characteristics of the Doppler signals, the performance of the eigenvector-based clutter filtering may exceed that of the IIR filtering. Thus, it has been required to appropriately set eigenvectors for the enhanced eigenvector-based clutter filtering.
  • XP007913995 " Nonparametric clutter rejection in Doppler ultrasound using principal component analysis" by Ahmed Elnokrashy et al. describes an ultrasound system according to the preamble of claim 1. Furthermore, this document discloses a method of setting eigenvectors suitable for providing a color flow image in which ultrasound signals are transmitted to and received from a target object to acquire first Doppler signals.
  • Embodiments for setting eigenvectors for clutter signal filtering are disclosed herein.
  • the invention is defined in claims 1 and 4.
  • the ultrasound system 100 may include a user input unit 110.
  • the user input unit 110 may allow a user to input a user instruction.
  • the user instruction may include information on the position and size of a region of interest (ROI) (e.g., a color box), which the user wants to set on a brightness mode (B-mode) image.
  • ROI region of interest
  • B-mode brightness mode
  • the user input unit 110 may include at least one of a control panel, a mouse, a keyboard, a touch screen, etc.
  • the ultrasound system 100 may further include a Doppler signal acquisition unit 120.
  • the Doppler signal acquisition unit 120 may be operable to alternately transmit and receive ultrasound signals to and from a target object (e.g., heart, blood flow, etc) in synchronization with a pulse repetition frequency (PRF).
  • the Doppler signal acquisition unit 120 may acquire Doppler signals corresponding to the ROI based on the received ultrasound signals. The acquisition of the Doppler signals will be described in detail by referring to FIG 2 .
  • FIG 2 is a block diagram showing an illustrative embodiment of the Doppler signal acquisition unit 120.
  • the Doppler signal acquisition unit 120 may include a transmit (Tx) signal generating section 121.
  • the Tx signal generating section 121 may be operable to generate a plurality of Tx signals. The generation of the Tx signals may be controlled by whether the current image mode is a B-mode, a C-mode, a D-mode, etc.
  • the Tx signal generating section 121 may generate Tx signals for forming a color flow image within the ROI consisting of a plurality of scan lines in the C-mode.
  • the Tx signal generating section 121 may repeatedly generate the Tx signals based on a predetermined ensemble number.
  • the Doppler signal acquisition unit 120 may further include an ultrasound probe 122 containing a plurality of elements for reciprocally converting ultrasound signals and electrical signals.
  • the ultrasound probe 122 may be operable to transmit ultrasound signals into a target object in response to the Tx signals.
  • the ultrasound probe 122 may be further operable to receive echo signals reflected from the target object to thereby output electrical receive signals, which are analog signals. The transmission and reception of the ultrasound signals are alternately carried out to output a plurality of electrical receive signals.
  • the Doppler signal acquisition unit 120 may further include a beam forming section 123.
  • the beam forming section 123 may be operable to convert the electrical receive signals into digital signals.
  • the beam forming section 123 may be further operable to apply delays to the digital signals in consideration of distances between the elements and focal points, thereby outputting digital receive-focused signals.
  • the Doppler signal acquisition unit 120 may further include a Doppler signal forming section 124 that may be operable to form Doppler signals based on the digital receive-focused signals.
  • the Doppler signals may include in-phase Doppler signals and quadrature phase signals.
  • the Doppler signals may also include clutter signals.
  • these Doppler signals may be referred to as "first Doppler signals.”
  • the Doppler signal acquisition unit 120 may form the first Doppler signals as many as the predetermined ensemble number for each of the scan lines within the ROI.
  • the ultrasound system 100 may further include a processing unit 130 coupled to the Doppler signal acquisition unit 120.
  • the processing unit 130 may be operable to set at least one eigenvector based on the first Doppler signals.
  • the processing unit 130 may be further operable to perform clutter signal filtering upon the first Doppler signals by using eigenvectors thereof to remove the clutter signals.
  • the processing unit 130 may be operable to form a color flow image by using the Doppler signals from which the clutter signals are filtered out. The operation of the processing unit 130 will be described in detail by referring to FIG 3 .
  • FIG 3 is a block diagram showing an illustrative embodiment of the processing unit 130.
  • the processing unit 130 may include a covariance matrix computing section 131.
  • the covariance matrix computing section 131 may be operable to compute a covariance matrix by using the plurality of first Doppler signals provided from the Doppler signal acquisition unit 120.
  • the covariance matrix computing section 131 may be operable to select one of the scan lines, which are included in the ROI, and compute the covariance matrix by using the first Doppler signals corresponding to the entire pixels on the selected scan line.
  • the covariance matrix computing section 131 may be operable to select one of the scan lines, and compute the covariance matrix by using the first Doppler signals corresponding to a predetermined number of pixels on the selected scan line. In yet another embodiment, the covariance matrix computing section 131 may be operable to compute the covariance matrix by using the first Doppler signals corresponding to the entire pixels of the scan lines on the ROI.
  • the covariance matrix may be computed by using various well-known methods. Thus, the detailed descriptions thereof will be omitted herein.
  • the processing unit 130 may further include an eigenvector computing section 132.
  • the eigenvector computing section 132 may be operable to compute a plurality of eigenvalues by using the computed covariance matrix and eigenvectors corresponding to the respective eigenvalues.
  • the eigenvalues and eigenvectors may be computed by using various well-known methods. As such, the detailed explanations thereof will be omitted herein.
  • the processing unit 130 may further include an eigenvector setting section 133.
  • the eigenvector setting section 133 may be operable to set at least one eigenvector for performing clutter signal filtering upon the first Doppler signals by using the plurality of eigenvectors (or both eigenvalues and eigenvectors).
  • the eigenvector setting section 133 may project the first Doppler signals corresponding to the respective pixels on the selected scan line along the respective eigenvectors.
  • the projected first Doppler signals will be referred to as "second Doppler signals.”
  • the second Doppler signals may be obtained as many as the number of the eigenvectors.
  • the eigenvector setting section 133 may be operable to compute component values from the second Doppler signals for the respective pixels.
  • the component values may be projected values of the second Doppler signals along the respective eigenvectors.
  • the eigenvector setting section 133 may be operable to compute an inner product through the equation (1) for the first Doppler signals corresponding to the respective pixels on the selected scan line and eigenvectors e 1 -e 10 computed in the eigenvector computing section 132, thereby computing the component values of the second Doppler signals for the respective pixels.
  • the eigenvector setting section 133 may be further operable to compute correlation values between the component values of the first Doppler signals and the component values of the second Doppler signals (i.e., amplitudes of the first and second Doppler signals).
  • the eigenvector setting section 133 may compare the computed correlation values with a predetermined threshold to detect the component values of the second Doppler signals greater than the predetermined threshold.
  • the eigenvector setting section 133 may be operable to set the eigenvectors corresponding to the detected component values as eigenvectors for clutter signal filtering.
  • FIG 4 shows graphs indicative of component values of the Doppler signals.
  • reference numerals "211-220" show graphs indicative of component values of the second Doppler signals (hereinafter, referred to as “first component graphs”).
  • reference numeral “230” shows a graph indicative of component values of the first Doppler signals (hereinafter, referred to as “second component graph”).
  • a horizontal direction (X-axis) represents positions of the pixels (i.e., depths) and a vertical direction (Y-axis) represents the component values (i.e., amplitudes) of the Doppler signals.
  • the portions of relatively large component values may correspond to blood vessels, which may be a possible source of the clutter signals.
  • the eigenvector setting section 133 may be operable to detect the component values of the second Doppler signals whose correlation values are greater than the predetermined threshold (e.g., the component values corresponding to first graphs 219 and 220 in FIG 4 ).
  • the eigenvector setting section 133 may be further operable to set eigenvectors corresponding to the component values e 9 -e 10 of the detected second Doppler signals as the eigenvectors for the clutter signal filtering.
  • FIG 5 is a graph showing Doppler frequency estimates of the Doppler signals.
  • reference numeral "310" represents Doppler frequencies of original Doppler signals obtained at a vessel portion (i.e., first Doppler signals).
  • reference numeral "320” represents Doppler frequencies of the Doppler signals resulting from the clutter signal filtering upon the first Doppler signals using the eigenvectors e 9 and e 10 , which are set in the eigenvector setting section 133.
  • Reference numeral “330” represents Doppler frequencies of the Doppler signals resulting from the clutter signal filtering upon the first Doppler signals using the eigenvector e 10 , which has been set in the eigenvector setting section 133.
  • the clutter signal filtering using the eigenvectors e 9 and e 10 has a better performance than the clutter signal filtering using the eigenvector e 10 .
  • the eigenvector setting section 133 may be operable to perform the clutter signal filtering upon the first Doppler signals by sequentially using the eigenvectors computed in the eigenvector computing section 132 to thereby form clutter signal filtered Doppler signals (hereinafter, referred to as "third Doppler signals").
  • the first Doppler signals may be filtered in an order determined by the magnitudes of the eigenvalues of the respective eigenvectors.
  • the eigenvector setting section 133 may be further operable to compute component values of the third Doppler signals for each of the pixels.
  • the component values may be a phase difference between third Doppler signals corresponding to an n th sample (or ensemble) and a (n-1) th sample (or ensemble) at each of the pixels, wherein n is a positive integer equal to or greater than 2.
  • the eigenvector setting section 133 may be further operable to set eigenvectors for clutter signal filtering by using the computed component values.
  • the eigenvector setting section 133 may be operable to set an eigenvector, which makes the phase difference kept to have the same sign, as the eigenvector for the clutter signal filtering.
  • the eigenvector setting section 133 may be operable to perform the clutter signal filtering upon the first Doppler signals by using the eigenvector having the largest eigenvalue (e.g., eigenvector e 10 ) among the plurality of eigenvectors e 1 to e 10 to form the third Doppler signals.
  • the eigenvector setting section 133 may be further operable to compute phase differences between the third Doppler signals corresponding to an n th sample (or ensemble) and a (n+1) th sample (or ensemble) for each of the pixels.
  • the eigenvector setting section 133 may be operable to detect a sign change of the detected phase differences. If the detected sign change is not maintained in the same sign, i.e., the sign is changed from plus (+) to minus (-) or vice versa, then the clutter signal filtering may be performed upon the first Doppler signals by using the eigenvectors having the first and second largest eigenvalues, e.g., eigenvectors e 10 and e 9 to form the third Doppler signals. Thereafter, the eigenvector setting section 133 may be operable to detect a sign change of the phase differences for the third Doppler signals in the same manner described above.
  • FIG 6 is a graph showing a trajectory of the phase differences of the third Doppler signals, in which the clutter signals are filtered by using two eigenvectors e 9 and e 10 .
  • the eigenvector setting section 133 may be operable to perform the clutter signal filtering upon the first Doppler signals by using the eigenvectors having the first to third largest eigenvalues, e.g., eigenvectors e 8 -e 10 , to form the third Doppler signals. Thereafter, the eigenvector setting section 133 may detect a sign change of the phase differences for the third Doppler signals.
  • FIG 7 is a graph showing a trajectory of phase differences of the third Doppler signals, in which the clutter signals are filtered by using the three eigenvectors e 8 to e 10 . If it is determined that the sign change of the detected phase differences is maintained in the same sign, i.e., the sign of the phase differences is not changed, then the eigenvector setting section 133 may set the eigenvectors of the eigenvectors e 8 to e 10 as the eigenvectors for the clutter signal filtering.
  • PCA represents an abbreviation of Principal Component Analysis.
  • the eigenvectors for the clutter signal filtering are set by using the eigenvectors in a magnitude order of the eigenvalues of the entire eigenvectors in order to detect the sign change of the phase differences
  • the setting of the eigenvectors for the clutter signal filtering may not be limited thereto.
  • the eigenvectors for the clutter signal filtering may be set by using the eigenvectors in a magnitude order of the eigenvalues of the eigenvectors corresponding to the component values e 9 -e 10 of the detected second Doppler signals in FIG 4 .
  • the processing unit 130 may further include a filtering section 134.
  • the filtering section may be operable to perform the clutter signal filtering upon the first Doppler signals by using the eigenvectors set in the eigenvector setting section 133.
  • the processing unit 130 may further include an image forming section 135.
  • the image forming section 135 may be operable to form a color flow image by using the Doppler signals with the clutter signals filtered.
  • the ultrasound system 100 may further include a display unit 140.
  • the display unit 140 may be embodied with any display capable of displaying the ultrasound images such as a B-mode image, a color flow image and the like.
  • the display unit 140 may include at least one of a CRT monitor, a LCD monitor and the like.

Claims (8)

  1. Ultraschallsystem (100), welches Folgendes aufweist:
    eine Doppler-Signalerlangungseinheit (120), welche dafür vorgesehen ist, Ultraschallsignale zu einem Zielobjekt zu übertragen und von demselben zu empfangen, um erste Doppler-Signale zu erlangen; und
    eine Verarbeitungseinheit (130), welche dafür vorgesehen ist, eine Vielzahl von Eigenvektoren durch Verwenden der ersten Doppler-Signale zu berechnen und zweite Doppler-Signale zu bilden, welche den Richtungen der berechneten Eigenvektoren entsprechen,
    dadurch gekennzeichnet, dass
    die Verarbeitungseinheit (130) dafür vorgesehen ist, Phasenverschiebungen zwischen nth-Samples und (n+1)th -Samples der zweiten Doppler-Signale zu berechnen, wobei n eine positive ganze Zahl gleich oder größer als 1 ist, und einen Vorzeichenwechsel der berechneten Phasenverschiebungen zu detektieren, um die Eigenvektoren, von denen das Vorzeichen der Phasendifferenz sich nicht geändert hat, als die Eigenvektoren für ein Filtern von Stördatensignalen unter der Vielzahl von Eigenvektoren festzulegen.
  2. Ultraschallsystem (100) nach Anspruch 1, wobei die Verarbeitungseinheit (130) Folgendes aufweist:
    einen Eigenvektor-Festlegungsabschnitt (133), welcher dafür vorgesehen ist, die Filterung von Stördatensignalen an den ersten Doppler-Signalen durch Verwenden der Vielzahl von Eigenvektoren in einer durch die Größe von Eigenwerten der jeweiligen Eigenvektoren festgelegten Reihenfolge durchzuführen, um die zweiten Doppler-Signale zu bilden, und die Eigenvektoren für das Filtern der Stördatensignale unter der Vielzahl von Eigenvektoren basierend auf den Phasenverschiebungen, die aus den zweiten Doppler-Signalen berechnet wurden, festzulegen; und
    einen Bilderzeugungsabschnitt (135), der dafür vorgesehen ist, ein Farbströmungsbild basierend auf den Stördatensignal gefilterten Doppler-Signalen zu erzeugen.
  3. Ultraschallsystem (100) nach Anspruch 2, wobei die Verarbeitungseinheit (130) des Weiteren Folgendes aufweist:
    einen Kovarianz-Matrix-Berechnungsabschnitt (131), welcher dafür vorgesehen ist, eine Kovarianz-Matrix unter Verwendung der ersten Doppler-Signale zu berechnen; und
    einen Eigenvektor-Berechnungsabschnitt (132), welcher dafür vorgesehen ist, die Vielzahl von Eigenvektoren auf der berechneten Kovarianz-Matrix zu berechnen.
  4. Verfahren zum Festlegen von Eigenvektoren, um ein Farbströmungsbild zu schaffen, welches Folgendes aufweist:
    a) Übertragen von Ultraschallsignalen zu einem Zielobjekt und Empfangen derselben, um erste Doppler-Signale zu erlangen;
    b) Berechnen einer Vielzahl von Eigenvektoren durch Verwenden der ersten Doppler-Signale;
    gekennzeichnet durch die folgenden Schritte:
    c) Bilden von zweiten Doppler-Signalen, welche den Richtungen der berechneten Eigenvektoren entsprechen;
    d) Berechnen von Phasenverschiebungen zwischen nth-Samples und (n+1)th-Samples der zweiten Doppler-Signale, wobei n eine positive ganze Zahl größer oder gleich 1 ist; und
    e) Detektieren eines Vorzeichenwechsels der berechneten Phasenverschiebungen;
    f) Festlegen der Eigenvektoren, von denen das Vorzeichen der Phasenverschiebung gleichbleibt, als die Eigenvektoren für ein Filtern von Stördatensignalen unter der Vielzahl von Eigenvektoren.
  5. Verfahren nach Anspruch 4, wobei der Schritt c) das Durchführen eines Filterns der Stördatensignale an den ersten Doppler-Signalen durch sequentielles Verwenden der Vielzahl von Eigenvektoren beinhaltet, um die zweiten Doppler-Signale zu bilden.
  6. Verfahren nach Anspruch 5, wobei das Filtern von Stördatensignalen in einer durch die Größe von Eigenwerten der jeweiligen Eigenvektoren festgelegten Reihenfolge durchgeführt wird.
  7. Verfahren nach Anspruch 4, wobei der Schritt b) Folgendes aufweist:
    Berechnen von Kovarianz-Matrizen unter Verwendung der ersten Doppler-Signale; und
    Berechnen der Vielzahl von Eigenvektoren unter Verwendung der Kovarianz-Matrizen.
  8. Verfahren nach Anspruch 4, welches des Weiteren Folgendes aufweist:
    Durchführen des Filterns der Stördatensignale an der Vielzahl von ersten Doppler-Signalen unter Verwendung der Eigenvektoren für das Filtern von Stördatensignalen;
    Erzeugen eines Farbströmungsbilds basierend auf den Stördaten gefilterten Doppler-Signalen; und
    Anzeigen des Farbströmungsbilds.
EP11177746.2A 2009-04-30 2010-04-29 Störechofilterung mit Eigenvektoren in einem Ultraschallsystem Active EP2392264B1 (de)

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KR101236472B1 (ko) 2007-10-15 2013-02-22 삼성전자주식회사 웨이퍼 베벨 영역 폴리싱 장치 및 그 장치에서의 연마종말점 검출 방법
KR100946710B1 (ko) 2007-10-24 2010-03-12 주식회사 메디슨 초음파 영상 처리 시스템 및 방법
JP5049773B2 (ja) * 2007-12-27 2012-10-17 株式会社東芝 超音波診断装置、超音波画像処理装置、超音波画像処理プログラム
KR20090128886A (ko) 2008-06-11 2009-12-16 삼성정밀화학 주식회사 무용매 상태하에서, 그리고 헤테로폴리산 촉매 및/또는흡수제의 존재하에서 글리세롤로부터 디클로로프로판올을제조하는 방법
JP5525867B2 (ja) * 2009-03-04 2014-06-18 株式会社東芝 超音波診断装置、画像処理装置、超音波診断装置の制御方法、及び画像処理方法
KR101121286B1 (ko) * 2009-07-31 2012-03-23 한국과학기술원 센서의 교정을 수행하는 초음파 시스템 및 방법

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EP2392264A1 (de) 2011-12-07
JP2010259799A (ja) 2010-11-18
EP2245988A1 (de) 2010-11-03
US20100280384A1 (en) 2010-11-04
US8306296B2 (en) 2012-11-06

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